KR20150136899A - Bio sensor having nano gap - Google Patents

Bio sensor having nano gap Download PDF

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Publication number
KR20150136899A
KR20150136899A KR1020140064587A KR20140064587A KR20150136899A KR 20150136899 A KR20150136899 A KR 20150136899A KR 1020140064587 A KR1020140064587 A KR 1020140064587A KR 20140064587 A KR20140064587 A KR 20140064587A KR 20150136899 A KR20150136899 A KR 20150136899A
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South Korea
Prior art keywords
nanogap
electrodes
nanoparticles
biosensor
biosensor according
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KR1020140064587A
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Korean (ko)
Inventor
김도균
이지윤
함철호
박현규
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주식회사 미코
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Priority to KR1020140064587A priority Critical patent/KR20150136899A/en
Priority to PCT/KR2015/005070 priority patent/WO2015182918A1/en
Publication of KR20150136899A publication Critical patent/KR20150136899A/en

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    • CCHEMISTRY; METALLURGY
    • C12BIOCHEMISTRY; BEER; SPIRITS; WINE; VINEGAR; MICROBIOLOGY; ENZYMOLOGY; MUTATION OR GENETIC ENGINEERING
    • C12QMEASURING OR TESTING PROCESSES INVOLVING ENZYMES, NUCLEIC ACIDS OR MICROORGANISMS; COMPOSITIONS OR TEST PAPERS THEREFOR; PROCESSES OF PREPARING SUCH COMPOSITIONS; CONDITION-RESPONSIVE CONTROL IN MICROBIOLOGICAL OR ENZYMOLOGICAL PROCESSES
    • C12Q1/00Measuring or testing processes involving enzymes, nucleic acids or microorganisms; Compositions therefor; Processes of preparing such compositions
    • C12Q1/68Measuring or testing processes involving enzymes, nucleic acids or microorganisms; Compositions therefor; Processes of preparing such compositions involving nucleic acids
    • GPHYSICS
    • G01MEASURING; TESTING
    • G01NINVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N27/00Investigating or analysing materials by the use of electric, electrochemical, or magnetic means
    • G01N27/26Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating electrochemical variables; by using electrolysis or electrophoresis
    • GPHYSICS
    • G01MEASURING; TESTING
    • G01NINVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N33/00Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
    • G01N33/48Biological material, e.g. blood, urine; Haemocytometers
    • G01N33/50Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing
    • G01N33/53Immunoassay; Biospecific binding assay; Materials therefor
    • GPHYSICS
    • G01MEASURING; TESTING
    • G01NINVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N33/00Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
    • G01N33/48Biological material, e.g. blood, urine; Haemocytometers
    • G01N33/50Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing
    • G01N33/68Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing involving proteins, peptides or amino acids

Abstract

A biosensor comprises: a pair of electrodes, where a voltage is supplied, having a nanogap therebetween; connectors positioned in each electrode in the nanogap to connect a first marker coupled with a biosubstance introduced to the nanogap to each adjacent electrode; and nanoparticles positioned in the nanogap to enable a second marker coupled with the biosubstance to be connected to an outer surface thereof.

Description

TECHNICAL FIELD [0001] The present invention relates to a biosensor having a nanogap (BIO SENSOR HAVING NANO GAP)

The present invention relates to a biosensor having a nanogap, and more particularly, to a biosensor for sensing a specific biomaterial existing in an organism through a nanogap.

Generally, a biosensor is a device for detecting a specific biomaterial such as an antigen-antibody of a protein, an enzyme of a DNA or a microorganism through a biological reaction between them or with them. Such a biosensor has a method of detecting by chemical, optical and electrical methods. Among them, recently, an electric method has been spotlighted because of its simple structure of equipment and low loss of sensed signals.

Specifically, in the biosensor of the electrical method, a connecting material that causes a biological reaction with the specific biomaterial is connected to each of the electrodes between a pair of facing electrodes, and the specific biomaterial contacts the connecting material The electrodes are connected to each other through a reaction with each other, so that the specific biomaterial is detected by an electrical signal generated from a voltage supplied from the outside.

At this time, since the electrodes are substantially made of biomaterials having high insulation characteristics, when the distance between the electrodes is relatively large in units of microns, the electrical signal is not generated. Therefore, It is necessary to form the gap between the electrodes so as to be very narrow as nano size so that the electrical signal can be detected by a specific bio material.

However, when the gap between the electrodes is formed to be very narrow as a nano size, the electrical signal is basically very weakly generated due to the material insulation characteristic of the specific bio material. Therefore, There is a problem in that it is difficult to distinguish whether it is due to an external factor such as biomaterial or other noise.

Korean Patent Application Publication No. 10-2010-0091751 (published on August 18, 2010, a sensor having a nanogap and a manufacturing method thereof) Korean Patent Laid-Open Publication No. 10-2012-0065791 (Publication date: 2012.06.21, Nanosensor and target molecule sensing method using the same)

The present invention provides a biosensor having a nanogap capable of amplifying an electrical signal generated when sensing a biomaterial.

According to an aspect of the present invention, a biosensor includes a pair of electrodes, a connector, and nanoparticles.

The electrodes are supplied with a voltage having a nanogap between them. The connector connects the first marker positioned at each of the electrodes in the nanogap to each of the adjacent electrodes. The first marker is coupled to the bio-material that is introduced into the nanogap from the outside. The nanoparticles are positioned in the nanogap, and a second marker, which is bonded to the biomaterial, is connected to the surface.

The nanoparticles according to one embodiment may be made of an insulating material. Specifically, the nanoparticles may include metal oxides in which the cation is trivalent or tetravalent.

The size (W) of the nanoparticle according to one embodiment may be in the range of 0.1G? W? 25G when the nanogap is G.

The linker according to an embodiment may include any one selected from the group consisting of protein G, protein A, polyethylenimine, and carbonyldiimidazole .

The connector according to another embodiment may comprise an immobilized enzyme or a self assembled monolayer.

The connector according to another embodiment may include a carboxyl group or an amine group contained in each of the electrodes.

Any one of the first and second markers and the biomaterial according to an embodiment may include an antibody and the other may include an antigen.

According to another aspect of the present invention, there is provided a biosensor comprising a pair of electrodes, a connector and nanoparticles.

The electrodes are supplied with a voltage having a nanogap between them. The connector is connected to each of the electrodes in the nanogap, and is coupled to the bio-material flowing into the nanogap from the outside. The nanoparticles are positioned in the nanogap, and a reactor reacting with the biomaterial is connected to the surface.

The connector according to an embodiment includes any one selected from the group consisting of poly-L-lysine, probe oligonucleotide, oligopeptide, and carbonyldiimidazole. can do.

The connector according to another embodiment may include a combination of nickel-nitrilotriacetic acid and gold or a self assembled monolayer.

The biomaterial according to an embodiment may include DNA in a foreign body, and the reactor may include complementary DNA (cDNA).

The biomaterial according to another embodiment may include a microorganism, and the reactor may include a lectin.

According to the biosensor having a nanogap of the present invention, a bio-material flowing into a nanogap between a pair of electrodes to which a voltage is supplied connects the electrodes through nanoparticles positioned in the nanogap, The generated electrical signal can be amplified. As a result, the bio-material can be precisely distinguished and detected through the amplified electrical signal, and reproducibility can be stably ensured.

FIG. 1 is a configuration diagram conceptually showing a biosensor according to an embodiment of the present invention.
2 is a graph for explaining an effect of amplifying an electrical signal when sensing a bio material through the biosensor shown in FIG.
FIG. 3 is a configuration diagram conceptually showing a biosensor according to another embodiment of the present invention.
FIG. 4 is a configuration diagram conceptually showing a biosensor according to another embodiment of the present invention.

Hereinafter, a biosensor according to an embodiment of the present invention will be described in detail with reference to the accompanying drawings. The present invention is capable of various modifications and various forms, and specific embodiments are illustrated in the drawings and described in detail in the text. It should be understood, however, that the invention is not intended to be limited to the particular forms disclosed, but on the contrary, is intended to cover all modifications, equivalents, and alternatives falling within the spirit and scope of the invention. Like reference numerals are used for like elements in describing each drawing. In the accompanying drawings, the dimensions of the structures are enlarged to illustrate the present invention in order to clarify the present invention.

The terms first, second, etc. may be used to describe various components, but the components should not be limited by the terms. The terms are used only for the purpose of distinguishing one component from another. For example, without departing from the scope of the present invention, the first component may be referred to as a second component, and similarly, the second component may also be referred to as a first component.

The terminology used in this application is used only to describe a specific embodiment and is not intended to limit the invention. The singular expressions include plural expressions unless the context clearly dictates otherwise. In this application, the terms "comprises", "having", and the like are used to specify that a feature, a number, a step, an operation, an element, a part or a combination thereof is described in the specification, But do not preclude the presence or addition of one or more other features, integers, steps, operations, components, parts, or combinations thereof.

Unless defined otherwise, all terms used herein, including technical or scientific terms, have the same meaning as commonly understood by one of ordinary skill in the art to which this invention belongs. Terms such as those defined in commonly used dictionaries are to be interpreted as having a meaning consistent with the contextual meaning of the related art and are to be interpreted as either ideal or overly formal in the sense of the present application Do not.

FIG. 1 is a block diagram conceptually showing a biosensor according to an embodiment of the present invention. FIG. 2 is a block diagram illustrating the effect of electrical signal amplification when sensing a bio material through the biosensor shown in FIG. Graph.

Referring to FIGS. 1 and 2, a biosensor 100 according to an embodiment of the present invention includes a pair of electrodes 110, a connector 120, and nanoparticles 130.

The electrodes 110 have a nanogap 112 therebetween and are supplied with a voltage from the outside. The nanogap 112 may have a spacing between about 100 and 1000 nm. A method of forming the nano gap 112 will be briefly described. First, an oxide film is formed on a substrate made of a single crystal silicon substrate through a thermal oxidation process or a chemical vapor deposition process. Next, a first nitride film is formed on the oxide film through a chemical vapor deposition process. Next, a pattern film having an opening having a micro size of about 1 to 2 탆 selectively exposing the first nitride film is formed on the first nitride film. Next, the first nitride film is etched using the pattern film as an etching mask to form a first nitride film pattern having a first gap. Next, the patterned film is removed through an ashing or stripping process. Next, a second nitride layer is formed through a chemical vapor deposition process or an atomic layer deposition process along the upper surface of the first nitride film pattern and the sidewalls and the bottom surface of the first gap. Next, the second nitride film is anisotropically etched to form a second nitride film pattern having a second gap of about 100 to 1000 nm on the sidewall of the first gap. Then, the oxide film is etched using the second nitride film pattern as an etching mask to form an oxide film pattern having a third nano-sized gap equal to the second gap. Next, electrodes 110 including a gate insulating film and a gate conductive film pattern are formed to have the second gap on the oxide film pattern.

At this time, the electrodes 110 may be made of a noble metal material such as gold (Au) or silver (Ag), which is highly conductive for electrical sensing of the bio-material 10 having a high insulation characteristic without forming an oxide film.

The coupler 120 is connected to each of the electrodes 110 at the nanogap 112 of the electrodes 110. Specifically, the connector 120 connects the first marker 122, which is coupled with the bio-material 10 flowing from the outside to the nanogap 112 at the nanogap 112, to the electrode 110 adjacent thereto. In this case, the first marker 122 may be indirectly connected to the electrode 110 while being coupled to the connector 120, because the first marker 122 may not be directly connected to the electrode 110 due to its material properties.

Here, the first marker 122 may be an antibody and the bio material 10 may be an antigen biologically bound to the antibody so that the biosensor 100 of the present embodiment can detect a substance of a protein type. Although the first marker 122 may be an antigen and the bio material 10 may be an antibody, it is common to detect an antigen rather than an antibody. Therefore, in the following description, the first marker 122 Antibody, and the biomaterial 10 is an antigen.

In order to connect the first marker 122, which is an antibody, to the electrode 110, the connector 120 is formed of a protein G, a protein A, a polyethylenimine and a carbonyldiimide And carbonyldiimidazole. The term " carbonyldiimidazole " In this case, if the connector 120 includes polyethyleneimine, the electrode 110 is coated with the polyethyleneimine and then the reactor 232 is formed of glutaraldehyde to form the first marker 122 ). ≪ / RTI >

Alternatively, the coupler 120 may comprise an immobilized enzyme or self assembled monolayer. In this case, when the coupler 120 includes a self-assembled monolayer structure, it is treated with 11-mercaptoundecanoic acid (MUA), and then immobilized in the middle of the reaction with EDC / NHS and zero linkers And finally removed away) to form the reactor 232 and join the first marker 122. Here, the reactor 232 formed according to the fixed activation reaction (EDC / NHS) may include a carboxyl group or an amine group. Meanwhile, when the electrode 110 is made of gold (Au), the first marker 122 may be directly connected to the electrode 110 by a direct adsorption method.

The nanoparticles 130 are nano-sized and located in the nanogaps 112 of the electrodes 110. The nanoparticles 130 are connected to a second marker 132, which is similar to the first marker 122 to which the bio-material 10, which is an antigen, is bound.

According to this configuration, the biosensor 100 can be configured such that the bio-material 10, which is an antigen introduced from the outside, is coupled to the first and second markers 122 and 132 through the nanoparticles 130, The electrodes 110 are connected to each other so that the biomaterial 10 is sensed through an electrical signal generated from a voltage supplied from the outside. Here, the electrical signal may include a current generated by electrons flowing due to the connection of the electrodes 110. Alternatively, the electrical signal may include any electrical data that can be measured, such as resistance, impedance, etc., in addition to the current.

Therefore, it is necessary that the nanoparticles 130 are made of an insulating material so that an electrical signal is generated only by the bio-material 10 to be sensed, that is, the electrodes 110 are not short-circuited to each other. Specifically, the nanoparticles 130 may be formed of a metal oxide-type material having an insulating property and being capable of being manufactured in a nano-size. More specifically, the nanoparticles 130 may be composed of metal oxides whose cations are trivalent or tetravalent. For example, the nanoparticles 130 may be formed of a material selected from the group consisting of alumina, bismuth oxide, cobalt oxide, copper oxide, dysprosium oxide, erbium oxide, A metal oxide such as europium oxide, gadolinium oxide, holmium oxide, iron oxide, lanthanum oxide, manganese oxide, neodymium oxide, But are not limited to, nickel oxide, polystyrene, antimony oxide, silicon dioxide, tin oxide, titanium dioxide, tungsten trioxide, zirconia zirconia, indium oxide, and zinc oxide.

When the nanoparticles 130 are supplied to the electrodes 110 of the biosensor 100 while the voltages are gradually increased while the nanoparticles 130 are positioned in the nanogaps 112 between the electrodes 110, A schottky effect that increases the electron emission proceeds, resulting in the amplification of an electrical signal generated from the bio-material 10, for example, a current.

This is because the first marker 122, which is an antibody, is well-connected to each of the electrodes 110 using Protein G as a connector 120 as a connector 120, and silicon dioxide having a carboxyl group as the nanoparticles 130 the second markers 132 are connected to each other through the fixed activation reaction (EDC / NHS) using silicon dioxide to increase the voltage of the electrodes 110, 2 can be seen from the graph.

2, when the voltage is increased to the electrodes 110 without the nanoparticles 130, the nanoparticles 130 of the present invention are applied to the electrodes (not shown) When the voltage is increased in the electrodes 110, the current value increases sharply as shown in a graph G2. In particular, when the voltage of the nanoparticles 130 of the present invention is raised in the nano gap 112, the current value of the nanoparticles 130 is very rapidly increased from the "P" , Respectively. This is because the "P" view of the graph G2 is formed when a potential barrier of additional connecting materials such as the connector 120, the nanoparticles 130, the first and second markers 122 and 132 except for the bio material 10 is formed As a voltage, when a higher voltage is applied, it means that the above-described schottky effect is actively progressing.

Accordingly, it is possible to analyze the sensed bio-material 10 by calculating electrical characteristic values such as resistance, impedance and dielectric constant using the current value amplified through the nanoparticles 130 of the present invention. Specifically, the detected bio material 10 is quantitatively classified according to the concentration, and then the type of the bio material 10 can be analyzed through the difference of the electrical characteristic values. In this case, since the current value measured when the biosensor 10 is sensed in a solution state is directly affected by the solution, it is preferable to sense the biosensor 10 in a dry state .

On the other hand, the nanogap 112 between the electrodes 110 is about 100 to 1000 nm according to the manufacturing method described above, whereas the biomaterial 10, which is an antigen to be detected, is significantly smaller than the nanogap 112 The nanoparticles 130 located in the nano gap 112 of the present invention serve as a bridge between the electrodes 110 by the bio material 10 so that they are connected to each other . The nanoparticle 130 needs to have a size W of about 0.1 G or more when the nanogap 112 is G so as to serve as the bridge. Conversely, the nanoparticles 130 may preferably have a size (W) of at most about 25 G in a range that can stabilize the bridge function, since the arc portion may serve as the bridge. Accordingly, the size (W) of the nanoparticles 130 can be included in the range of 0.1G? W? 25G.

As described above, the bio material 10 flowing into the nanogap 112 between the pair of electrodes 110 to which the voltage is supplied passes through the nanoparticles 130 located in the nanogap 112, Thereby amplifying an electrical signal generated thereby, for example, a current value. Accordingly, by ensuring a resolution that is increased according to the concentration through the amplified current value, the biomaterial 10 to be sensed can be accurately distinguished from the noise and detected, and the reproducibility can be stably ensured.

In addition, since the detection limit can be increased by amplifying the sensed current value using the nanoparticles 130, even when the concentration of the biomaterial 10 to be sensed is small, You can expect more.

Further, in the state where the electrodes 110 are connected to the bio material 10 through the nanoparticles 130, the abnormal reaction part is cleaned using a washing buffer, and then the amplified current value is measured. Reproducibility can be ensured.

FIG. 3 is a configuration diagram conceptually showing a biosensor according to another embodiment of the present invention.

3, a biosensor 200 according to another embodiment of the present invention includes a pair of electrodes 210 having a nano gap 212 and supplied with a voltage from the outside, a nano gap 212, A plurality of electrodes 220 connected to the electrodes 210 and coupled to the bio-material 20 from the outside, specifically a plurality of external DNA 20 and a nanogap 212, (230) connected to the surface of the reactor (232). Here, since the electrodes 210 are substantially the same as the electrodes 110 shown in FIG. 1 (110 of FIG. 1), a detailed description thereof will be omitted.

The linker 220 is composed of poly-L-lysine, probe oligonucleotide, oligopeptide and carbonyldiimidazole so as to be able to bind to the foreign DNA 20. And < / RTI >

Alternatively, the coupler 220 may comprise a nickel-nitrilotriacetic acid-gold combination or a self assembled monolayer. When the connector 220 includes a self-assembled monolayer structure, it is treated with 3,3'-dithioldipropionic acid to react with streptavidin after a fixed activation reaction (EDC / NHS) And is bound to the stranded DNA 20.

The nanoparticles 230 are made of an insulating material capable of being manufactured in a nano size so as not to short-circuit the electrodes 210 in the nanogaps 212. Therefore, the material of the nanoparticles 230 of the present embodiment is substantially the same as the nanoparticles (130 of FIG. 1) described in FIG. 1, and thus a detailed description thereof will be omitted. In addition, the reactor 232 includes complementary DNA (cDNA) to react with and bind to the DNA 20 on the surface of the nanoparticles 230.

Thus, when the reactor 232 of the complementary DNA (cDNA) reacts with and binds to the external DNA 20 coupled to the connector 220, the electrodes 210 are connected to each other at the nanogaps 212 , And an electric signal, that is, a current value is sensed from a voltage supplied from the outside.

1, the schottky effect proceeds through the nanoparticles 230 located in the nanogap 212 when the voltage is gradually increased to the electrodes 210 in the embodiment of FIG. 1, The current value can be amplified and detected.

Therefore, as in the embodiment with reference to FIG. 1, by securing a resolution that is increased according to the concentration through the amplified current value, it is possible not only to detect the foreign DNA 20 to be sensed accurately and discriminate it from noise, It can be stably secured. In addition, by amplifying the sensed current value by using the nanoparticles 230, the detection limit can be increased, and even when the concentration of the foreign DNA 20 is minute, it can be detected sufficiently.

FIG. 4 is a configuration diagram conceptually showing a biosensor according to another embodiment of the present invention.

4, a biosensor 300 according to another embodiment of the present invention includes a pair of electrodes 310 having a nanogap 312 and supplied with a voltage from the outside, a nano gap 312, The microorganisms 30 are connected to each of the electrodes 310 and connected to each of the electrodes 310 and connected to the bio-material 30, specifically, the connecting unit 320 to which the microorganisms 30 such as enzymes are coupled and the nanogap 312, The reacting reactor 332 comprises nanoparticles 330 connected to the surface. Here, since the electrodes 310 are substantially the same as the electrodes 110 shown in FIG. 1 (110 of FIG. 1), detailed description thereof will be omitted.

The connector 320 includes a carrier which is present in the biological membrane of the microorganism 30 and serves to mediate the transportation of the microorganism 30. Accordingly, the connector 320 may include various types of carriers depending on the type of the microorganism 30 to be detected.

The nanoparticles 330 are made of an insulating material which can be manufactured in a nano size so as not to short-circuit the electrodes 310 in the nanogap 312. Therefore, the material of the nanoparticles 330 of the present embodiment is substantially the same as the nanoparticles (130 of FIG. 1) described in FIG. 1, so that a detailed description thereof will be omitted. In addition, the reactor 332 includes a lectin to react and bind with the microorganism 30 on the surface of the nanoparticles 330.

When the lectin reactor 332 reacts with the microorganisms 30 coupled with the carrier 320 as a carrier, the electrodes 310 are connected to each other at the nanogaps 312 , And an electric signal, that is, a current value is sensed from a voltage supplied from the outside.

1, when the voltage is gradually increased to the electrodes 310, the schottky effect is progressed through the nanoparticles 330 located in the nano gap 312, The current value can be amplified and detected.

Accordingly, as in the embodiment with reference to FIG. 1, by securing a resolution that is increased according to the concentration through the amplified current value, it is possible not only to detect the microorganisms 30 sensed accurately, but also to reproduce the reproducibility . Further, by amplifying the sensed current value by using the nanoparticles 330, the detection limit can be increased, and even when the concentration of the microorganism 30 is minute, it can be sufficiently detected.

It will be apparent to those skilled in the art that various modifications and variations can be made in the present invention without departing from the spirit or scope of the present invention as defined by the appended claims. It will be understood that the present invention can be changed.

As described above, in the biosensor of the present invention, a specific biomaterial such as an antigen-antibody, a DNA or an enzyme of a microorganism of a protein flowing into a nanogap between a pair of electrodes to which a voltage is supplied is located in the nanogap By connecting the electrodes to each other through nanoparticles and amplifying an electrical signal generated through the nanoparticles, the biomaterial can be accurately and stably detected.

10: Biomaterials 20: Foreign DNA
30: Microorganisms 100, 200, 300: Biosensor
110, 210 and 310: electrodes 112, 212 and 312: nano gap
120, 220, 320: connector 122: first marker
130, 230, 330: nanoparticles 132: second marker
232, 332: reactor

Claims (15)

A pair of electrodes having a nano-gap and supplied with a voltage;
A connector positioned at each of the electrodes in the nanogap to connect a first marker, which is coupled to the bio-material introduced into the nanogap from the outside, to each of the adjacent electrodes; And
And a nanoparticle positioned on the nanogap, the nanoparticle having a second marker coupled to the surface, the nanoparticle being coupled to the biomaterial.
The biosensor according to claim 1, wherein the nanoparticles are made of an insulating material. The biosensor according to claim 1, wherein the nanoparticles include metal oxides whose cations are trivalent or tetravalent. The biosensor according to claim 1, wherein the size (W) of the nanoparticles is in the range of 0.1G? W? 25G, where the nanogap is G. The method of claim 1, wherein the linker comprises any one selected from the group consisting of protein G, protein A, polyethylenimine, and carbonyldiimidazole. The biosensor is characterized by. The biosensor according to claim 1, wherein the connector comprises an immobilized enzyme or a self assembled monolayer. The biosensor according to claim 1, wherein one of the first and second markers and one of the biomaterials comprises an antibody and the other comprises an antigen. A pair of electrodes having a nano-gap and supplied with a voltage;
A coupling unit connected to each of the electrodes in the nano gap and coupled with a bio material introduced into the nanogap from the outside; And
And a nanoparticle positioned in the nanogap, the nanoparticle being connected to a surface of the reactor reacting with the biomaterial.
The biosensor according to claim 8, wherein the nanoparticles are made of an insulating material. The biosensor according to claim 8, wherein the nanoparticle includes a metal oxide having a trivalent or tetravalent cation. 9. The biosensor according to claim 8, wherein the size (W) of the nanoparticles is in the range of 0.1G? W? 25G when the nanogap is G. 9. The method of claim 8, wherein the linker is selected from the group consisting of poly-L-lysine, probe oligonucleotide, oligopeptide, and carbonyldiimidazole. Wherein the biosensor is a biosensor. The biosensor according to claim 8, wherein the connector comprises a nickel-nitrilotriacetic acid-gold combination or a self-assembled monolayer. The biosensor according to claim 8, wherein the biomaterial comprises foreign DNA and the reactor comprises complementary DNA (cDNA). The biosensor according to claim 8, wherein the biomaterial comprises a microorganism, and the reactor comprises lectin.
KR1020140064587A 2014-05-28 2014-05-28 Bio sensor having nano gap KR20150136899A (en)

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US20220099615A1 (en) * 2019-01-18 2022-03-31 Universal Sequencing Technology Corporation Devices, Methods, and Chemical Reagents for Biopolymer Sequencing

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US20120037515A1 (en) * 2009-04-15 2012-02-16 TheStateof Oregonactingbyand throughthestateBoard ofHigherEducationon behalf of thePortlandstateUniv Impedimetric sensors using dielectric nanoparticles
KR20110128754A (en) * 2010-05-24 2011-11-30 한국생명공학연구원 Electrical biosensor for detecting infinitesimal sample
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KR101779611B1 (en) * 2011-01-20 2017-09-18 엘지전자 주식회사 Cartridge for detecting target antigen and method for detecting target antigen using the same
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